Blood pump and pump unit

The present invention relates to a blood pump and a pump unit for pumping blood.

In open-heart surgery, a blood pump for pumping blood is used to maintain the blood circulation. A known blood pump includes a casing, an impeller rotatably arranged in the casing, and a driving mechanism causing the impeller to rotate, and causes the impeller to rotate by the driving mechanism to take blood into a channel inside the casing and pump the blood outside the casing.

In this type of blood pump, for example, a rotating shaft for the impeller penetrates the wall of the casing and projects from the casing, and a driving motor is connected to the rotating shaft. In an area where the rotating shaft penetrates the wall of the casing, an axial sealing structure is provided to prevent leakage of blood. However, because the axial sealing structure is in contact with the casing and the rotating shaft, red blood cells and other components in the blood may be damaged at these points of contact to cause hemolysis, and stagnant blood flow at the points of contact may cause a blood clot. In addition, an issue may arise with durability of the sealing.

To address the foregoing, a blood pump supporting an impeller in a casing in a noncontact manner has been known. Such a blood pump includes a driving mechanism that causes the impeller to rotate by interaction between a magnet provided to the impeller and another magnet arranged outside the casing and driven for rotation by a driving motor. In a narrow gap between the outer peripheral surface of the impeller and the inner peripheral surface of the casing, a dynamic bearing is provided that supports the impeller in the radial direction with the pressure of the blood pumped in through rotation of the impeller. Furthermore, a controllable magnetic bearing is provided that supports the impeller in the axis direction by placing a bearing magnet provided to the impeller and a magnet core provided to the casing face to face with each other in the radial direction and controlling the magnetic force of the magnetic core depending on the position of the impeller (see Patent Document 1, for example).

[Patent Document 1] Japanese Patent Application Laid-open No. 2006-226390

Problem to be Solved by the Invention

In the blood pump disclosed in Patent Document 1, the impeller includes vanes radially arranged on one side surface in the axis direction of a base, and a channel for defining a dynamic bearing is formed on the other side of the base. The casing includes a suction tube toward the center on the one side of the base with the vanes, and an ejection tube on the outer peripheral surface. With this blood pump, the vanes produce outward pressure in the radial direction through rotation of the impeller, whereby blood is sucked through the suction tube and pumped out through the ejection tube.

In the blood pump thus configured, however, when blood is sucked on one side of the base with the vanes, the other side has higher pressure than the one side of the base, i.e., a pressure difference occurs therebetween, resulting in axial thrust load to push the impeller toward the one side. Consequently, the axial center gets misaligned to cause defective operation of the blood pump. While the controllable magnetic bearing supports the impeller in the axis direction in the blood pump disclosed in Patent Document 1, this involves high manufacturing cost for providing a control circuit and the magnetic core. In addition, malfunction of the control circuit leads to loss of the function of the bearing, which makes it difficult to ensure high reliability.

In view of the problems described above, the present invention has an object to provide a blood pump and a pump unit that are configured to rotatably supporting an impeller in a casing in the radial direction in a noncontact manner and to support axial thrust load at low manufacturing cost, thereby enabling rotation also in the axial direction in a noncontact manner.

Means for Solving Problem

According to an aspect of the present invention, a blood pump includes: a rotating body rotatably placed inside a casing a magnetic coupling functioning as an axial bearing including a driven magnet that is a permanent magnet provided to the rotating body and a drive magnet that is a permanent magnet placed face to face with the driven magnet in a radial direction of the rotating body outside the casing to be magnetically coupled with the driven magnet; a drive that rotatably drives the drive magnet about an axis of the rotating body; a radial bearing that is a dynamic bearing having annular bearing surfaces centering on the axis on an inner wall of the casing and the rotating body, each of the annular bearing surfaces being arranged with a gap between the drive magnet and the driven magnet in the radial direction of the rotating body; and a closed impeller including a front shroud arranged on a front side in the axis direction in the rotating body, a rear shroud arranged on a rear side in the axis direction of the front shroud, and a vane arranged between the front shroud and the rear shroud.

With this blood pump, because the radial bearing and the axial bearing cause the rotating body to rotate in a noncontact state with respect to the casing, states leading to hemolysis or a blood clot can be prevented without the need for any shaft penetrating the casing or any axial sealing structure to prevent leakage of blood along the shaft. Furthermore, the impeller of this blood pump includes the front shroud arranged on the front side in the axis direction through which blood is taken in, the rear shroud arranged on the rear side in the axis direction of the front shroud, and the vane arranged between the front shroud and the rear shroud. Therefore, the blood flowing toward the rear side of the rear shroud produces pressure acting on the front side in the axis direction, and the blood flowing toward the front side of the front shroud produces pressure acting on the rear side in the axis direction. Consequently, the balance of the axial thrust load pushing the impeller in the axis direction can be adjusted, whereby defective operation is prevented with a simple axial bearing having a driven magnet and a drive magnet alone. Manufacturing cost can be thus reduced because no control circuit for adjusting the magnetic force of a magnet core is required.

Advantageously, in the blood pump, the radial bearing is also arranged, besides between the rotating body and the inner wall of the casing on the rear side of the rear shroud that is between the drive magnet and the driven magnet, between the rotating body and the inner wall of the casing on the front side of the front shroud.

With this blood pump, the radial bearings support both ends of the rotating body. Therefore, the radial load of the rotating body can be held in a more stable manner.

Advantageously, in the blood pump, the blood pump is configured to have a pump unit in which the rotating body including the driven magnet is placed inside the casing, and the radial bearing is provided between the rotating body and the inner wall of the casing, and a driving unit that includes the drive magnet and the drive, and the pump unit is detachably provided to the driving unit.

With this blood pump, the pump unit is detachably provided to the driving unit. The pump unit, which comes in contact with blood, is thus disposable as a consumable supply. By providing the pump unit that is economical with this configuration, running cost to purchase consumable supplies can be reduced.

Advantageously, in the blood pump, the driven magnet is provided to a cylindrical shaft included in the rotating body, and the drive magnet is arranged outside in a radial direction of the shaft with respect to the driven magnet.

With this blood pump, the shaft can be made compact, and the pump unit can thus be made compact, which facilitates its handling.

According to another aspect of the present invention, a pump unit of a blood pump that includes a rotating body rotatably placed inside a casing and is detachably provided to a driving unit rotatably driving the rotating body, includes: a driven magnet that is a permanent magnet provided to the rotating body in a face-to-face manner in a radial direction of the rotating body with a drive magnet that is a permanent magnet of the driving unit provided outside the casing to be rotatably driven about an axis of the rotating body, the driven magnet being magnetically coupled with the drive magnet to be a magnetic coupling functioning as an axial bearing; a radial bearing that is a dynamic bearing having annular bearing surfaces centering on the axis on an inner wall of the casing and the rotating body, each of the annular bearing surfaces being arranged with a gap between the drive magnet and the driven magnet in the radial direction of the rotating body; and a closed impeller including a front shroud arranged on a front side in the axis direction in the rotating body, a rear shroud arranged on a rear side in the axis direction of the front shroud, and a vane arranged between the front shroud and the rear shroud.

With this pump unit, because the rotating body is caused to rotate in a noncontact state with respect to the casing by the radial bearing and the axial bearing, states leading to hemolysis or a blood clot can be prevented without the need for any shaft penetrating the casing or any axial sealing structure to prevent leakage of blood along the shaft. Furthermore, the impeller of this pump unit includes the front shroud arranged on the front side in the axis direction through which blood is taken in, the rear shroud arranged on the rear side in the axis direction of the front shroud, and the vane arranged between the front shroud and the rear shroud. Therefore, the blood flowing toward the rear side of the rear shroud produces pressure acting on the front side in the axis direction, and the blood flowing toward the front side of the front shroud produces pressure acting on the rear side in the axis direction. Consequently, the balance of the axial thrust load pushing the impeller in the axis direction can be adjusted, whereby defective operation is prevented with a simple axial bearing having a driven magnet and a drive magnet alone. Manufacturing cost can be thus reduced because no control circuit for adjusting the magnetic force of a magnet core is required.

Effect of the Invention

The present invention enables the impeller to be rotatably supported in the casing in a noncontact manner both in the axial direction and the radial direction with low manufacturing cost, and eliminates the need for controlling magnetic force, thereby ensuring high reliability.

FIG. 1 is a schematic sectional view of a blood pump according to an embodiment of the present invention.

FIG. 2 is a sectional view along A-A in FIG. 1 .

FIG. 3 is a schematic sectional view of the blood pump illustrated in FIG. 1 in a detached state.

FIG. 4 is a schematic sectional view of a blood pump having an alternative structure according to the present embodiment.

10 pump unit

11 rotating body

11 A impeller

11 A 1 front shroud

11 A 1 a suction port

11 A 1 b cylindrical unit

11 A 1 c bearing surface (radial bearing)

11 A 2 rear shroud

11 A 3 vane

11 B shaft

11 B 1 bearing surface (radial bearing)

11 B 2 penetrating hole

11 B 3 driven magnet (axial bearing)

12 casing

12 A pumping unit

12 A 1 suction inlet

12 A 2 ejection outlet

12 A 3 bearing surface (radial bearing)

12 B bearing unit

12 B 1 bearing surface (radial bearing)

20 driving unit

21 container

22 driving motor (drive)

22 A output shaft

23 rotating member

23 A drive magnet (axial bearing)

24 lid member

24 A recess

P axis

Embodiments of a blood pump and a pump unit according to the present invention will now be explained in detail with reference to the accompanying drawings. These embodiments are not intended to limit the present invention. Constituent elements in the embodiments below include elements readily substituted by those skilled in the art and substantially equivalent elements.

FIG. 1 is a schematic sectional view of a blood pump according to an embodiment of the present invention. FIG. 2 is a sectional view along A-A in FIG. 1 . FIG. 3 is a schematic sectional view of the blood pump illustrated in FIG. 1 in a detached state. As illustrated in FIG. 1 , the blood pump according to the embodiment of the present invention includes a pump unit 10 and a driving unit 20 .

The pump unit 10 includes a rotating body 11 and a casing 12 .

The rotating body 11 has an impeller 11 A and a shaft 11 B. The impeller 11 A is configured as a closed impeller having a front shroud 11 A 1 , a rear shroud 11 A 2 , and a vane 11 A 3 . The front shroud 11 A 1 is formed in a substantially disk shape to define the outer diameter of a circle centering on an axis P about which the rotating body 11 rotates, and arranged on the front side in the axis P direction in the impeller 11 A. The front shroud 11 A 1 has, along the axis P on which it centers, a suction port 11 A 1 a penetrating therethrough for sucking blood. The rear shroud 11 A 2 is formed in a substantially disk shape to define the outer diameter of a circle centering on the axis P, and arranged on the rear side in the axis P direction (on the lower side of FIG. 1 ) in the impeller 11 A. The vane 11 A 3 is placed in a gap between the front shroud 11 A 1 and the rear shroud 11 A 2 . The vane 11 A 3 forms part of a spiral starting from the center and terminating at the outer peripheral end of the front shroud 11 A 1 to avoid the suction port 11 A 1 a of the front shroud 11 A 1 . A plurality of such vanes 11 A 3 is provided at regular intervals in the circumferential directions of the front shroud 11 A 1 and the rear shroud 11 A 2 . The outer peripheral rims of the front shroud 11 A 1 and the rear shroud 11 A 2 that have high pressure during pumping of blood are arranged on the outermost periphery of the rotating body 11 .

The shaft 11 B is formed in a cylindrical shape having a smaller diameter than that of each shroud 11 A 1 , 11 A 2 and centering on the axis P, and projects further toward the rear side in the axis P direction of the rear shroud 11 A 2 . On the outer periphery of the shaft 11 B, an annular bearing surface 11 B 1 centering on the axis P is formed. The shaft 11 B also has, along the axis P on which it centers, a penetrating hole 11 B 2 . The penetrating hole 11 B 2 is formed to penetrate the rear shroud 11 A 2 and to communicate with the suction port 11 A 1 a of the front shroud 11 A 1 through the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 . A driven magnet 11 B 3 is also provided to the shaft 11 B. The driven magnet 11 B 3 is a permanent magnet and is embedded in the shaft 11 B along the bearing surface 11 B 1 . A plurality of (e.g., four) such driven magnets 11 B 3 is formed in an annular shape centering on the axis P and is so arranged that S and N poles are alternately placed next to each other along the annular shape as illustrated in FIG. 2 .

The casing 12 forms an outer casing of the pump unit 10 and contains therein the rotating body 11 . The casing 12 has, on the front side in the axis P direction about which the rotating body 11 rotates, a suction inlet 12 A 1 for taking in blood. The casing 12 also has an ejection outlet 12 A 2 for pumping out blood to areas on the outer side in the radial direction of the impeller 11 A perpendicular to the axis P.

The casing 12 includes a pumping unit 12 A having an inner wall formed along the contour of the rotating body 11 , enclosing the impeller 11 A, and having the suction inlet 12 A 1 and the ejection outlet 12 A 2 ; and a bearing unit 12 B enclosing the shaft 11 B and projecting toward the rear side in the axis P direction of the pumping unit 12 A. The casing 12 is formed to have a certain gap between its inner wall and the contour of the rotating body 11 . In other words, the casing 12 is configured to have a noncontact operation state with respect to the rotating body 11 while containing therein the rotating body 11 . On the inner wall of the bearing unit 12 B of the casing 12 , an annular bearing surface 12 B 1 centering on the axis P is placed face to face with the bearing surface 11 B 1 formed on the shaft 11 B of the rotating body 11 with a certain gap in the radial direction of the rotating body 11 interposed therebetween.

The driving unit 20 is prepared by placing a driving motor (drive) 22 and a rotating member 23 in a bottomed cylindrical container 21 . The driving motor 22 is fixed inside the container 21 , and has an output shaft 22 A extending toward the front side along the axis P of the rotating body 11 . The rotating member 23 is fixed to the output shaft 22 A of the driving motor 22 and provided rotatably about the axis P through driving of the driving motor 22 . The rotating member 23 is formed in an annular shape centering on the axis P to enclose the bearing unit 12 B of the casing 12 of the pump unit 10 . In other words, the rotating member 23 encloses the shaft 11 B of the rotating body 11 in the casing 12 .

To the annular inner wall of the rotating member 23 , a drive magnet 23 A is provided. The drive magnet 23 A is a permanent magnet. A plurality of (e.g., four) such drive magnets 23 A is provided in an annular shape centering on the axis P and is so arranged that S and N poles are alternately placed next to each other along the annular shape as illustrated in FIG. 2 . The drive magnet 23 A is placed face to face with the driven magnet 11 B 3 in the radial direction of the rotating body 11 , thereby being magnetically coupled with the driven magnet 11 B 3 provided to the shaft 11 B of the rotating body 11 from outside of the casing 12 .

On the front side in the axis P direction of the container 21 , a lid member 24 is provided for hermetically closing the opening of the container 21 and covering the driving motor 22 and the rotating member 23 . The lid member 24 has a recess 24 A that is retracted in the annular shape of the rotating member 23 . Into the recess 24 A, the bearing unit 12 B of the casing 12 is inserted to place the shaft 11 B of the pump unit 10 in the annular shape of the rotating member 23 . As illustrated in FIG. 3 , the bearing unit 12 B of the casing 12 is detachably provided to the recess 24 A.

The blood pump thus configured drives, in a state where the bearing unit 12 B of the casing 12 is inserted into the recess 24 A of the lid member 24 , the driving motor 22 to cause the rotating member 23 to rotate about the axis P. When the rotating member 23 rotates, the drive magnet 23 A provided to the rotating member 23 rotates about the axis P. Along with this rotation, the driven magnet 11 B 3 magnetically coupled with the drive magnet 23 A also rotates. When the driven magnet 11 B 3 rotates, the rotating body 11 provided with the driven magnet 11 B 3 rotates substantially about the axis P. In this operation, because the driven magnet 11 B 3 is magnetically coupled with the drive magnet 23 A, suction force in the opposite direction to the movement in the axis P direction acts on the rotating body 11 provided with the driven magnet 11 B 3 . In other words, the driven magnet 11 B 3 and the drive magnet 23 A serve as a magnetic coupling functioning as an axial bearing that holds rotation of the rotating body 11 in the axis P direction.

When the rotating body 11 rotates, by the action of the vanes 11 A 3 , blood is taken inside the casing 12 through the suction inlet 12 A 1 . The blood is pumped through the suction port 11 A 1 a of the impeller 11 A into the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 , further pumped through this gap outward in the radial direction, and pumped outside the casing 12 through the ejection outlet 12 A 2 .

Part of the high-pressure blood pumped outward in the radial direction through the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 is not pumped outside the casing 12 through the ejection outlet 12 A 2 , and circulates in a comparatively low pressure area near the axis P inside the casing 12 . More specifically, on the outer periphery of the impeller 11 A, the high-pressure blood flows through the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 toward the front side of the front shroud 11 A 1 and the rear side of the rear shroud 11 A 2 . The blood flowing toward the front side of the front shroud 11 A 1 passes between the front surface of the front shroud 11 A 1 and the inner wall of the casing 12 toward the axis P, and returns to the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 through the suction port 11 A 1 a . On the other hand, the blood flowing toward the rear side of the rear shroud 11 A 2 passes between the rear surface of the rear shroud 11 A 2 and the inner wall of the casing 12 toward the axis P, further passes through the gap between the bearing surface 11 B 1 of the shaft 11 B and the bearing surface 12 B 1 of the casing 12 , and returns to the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 through the penetrating hole 11 B 2 .

Because the gap between the bearing surface 11 B 1 and the bearing surface 12 B 1 is formed in an annular shape centering on the axis P, the blood passes through this gap, and the bearing surface 11 B 1 and the bearing surface 12 B 1 serve as a radial bearing as a dynamic bearing that holds rotation of the rotating body 11 about the axis P in the radial direction with the blood working as a lubricating fluid. In this manner, the shaft 11 B is held in a position centering on the axis P. In other words, the radial position of the rotating body 11 is held in a noncontact state with respect to the casing 12 .

Accordingly, with this blood pump, because the radial bearing and the axial bearing cause the rotating body 11 to rotate in a noncontact state with respect to the casing 12 , states leading to hemolysis or a blood clot can be prevented without the need for any shaft penetrating the casing 12 or any axial sealing structure to prevent leakage of blood along the shaft.

In particular, the impeller 11 A of the pump unit 10 in this blood pump includes the front shroud 11 A 1 arranged on the front side in the axis P direction through which blood is taken in, the rear shroud 11 A 2 arranged on the rear side in the axis P direction of the front shroud 11 A 1 , and the vanes 11 A 3 arranged between the front shroud 11 A 1 and the rear shroud 11 A 2 . Therefore, the blood flowing toward the rear side of the rear shroud 11 A 2 produces pressure acting on the front side in the axis P direction, and the blood flowing toward the front side of the front shroud 11 A 1 produces pressure acting on the rear side in the axis P direction. Consequently, the axial thrust load pushing the impeller 11 A in the axis P direction can be adjusted, whereby defective operation is prevented with a simple axial bearing having the driven magnet 11 B 3 and the drive magnet 23 A alone. Manufacturing cost can be thus reduced because no control circuit for adjusting the magnetic force of a magnet core is required.

With this blood pump, the pump unit 10 is detachably provided to the driving unit 20 . The pump unit 10 , which comes in contact with blood, is thus disposable as a consumable supply. By providing the pump unit 10 that is economical with this configuration, running cost to purchase consumable supplies can be reduced.

In the blood pump, the driven magnet 11 B 3 is provided to the shaft 11 B formed in a cylindrical shape centering on the axis P, and the drive magnet 23 A is placed on the outer side in the radial direction of the shaft 11 B with respect to the driven magnet 11 B 3 . Therefore, as illustrated by the blood pump in FIG. 4 , the driven magnet 11 B 3 is provided to the shaft 11 B formed in an annular shape centering on the axis P, and the shaft 11 B and the bearing unit 12 B can be made compact compared with a configuration in which the drive magnet 23 A is placed on the inner side in the radial direction of the shaft 11 B with respect to the driven magnet 11 B 3 . Therefore, the pump unit 10 to be disposed as a consumable supply can be made compact, which facilitates its handling.

The blood pump according to the present embodiment includes a radial bearing each on the front side in the axis P direction and the rear side in the axis P direction of the rotating body 11 . The radial bearing on the rear side in the axis P direction of the rotating body 11 is, as described above, the gap between the bearing surface 11 B 1 and the bearing surface 12 B 1 that is placed between the driven magnet 11 B 3 and the drive magnet 23 A. The radial bearing on the front side in the axis P direction of the rotating body 11 is arranged on the front side of the front shroud 11 A 1 , except for between the driven magnet 11 B 3 and the drive magnet 23 A. More specifically, on the front side of the front shroud 11 A 1 , a cylindrical unit 11 A 1 b is formed to extend further toward the front side of the suction port 11 A 1 a . On the outer periphery of the cylindrical unit 11 A 1 b , an annular bearing surface 11 A 1 c centering on the axis P is provided. On the other hand, on the inner wall of the pumping unit 12 A of the casing 12 , an annular bearing surface 12 A 3 centering on the axis P is placed face to face with the bearing surface 11 A 1 c with a certain gap in the radial direction of the rotating body 11 interposed therebetween. The blood passes through the gap between the bearing surface 11 A 1 c and the bearing surface 12 A 3 , and the bearing surface 11 A 1 c and the bearing surface 12 A 3 serve as a radial bearing as a dynamic bearing that holds rotation of the rotating body 11 about the axis P in the radial direction with the blood working as a lubricating fluid. In this manner, the impeller 11 A is held in a position centering on the axis P. By thus providing the radial bearings on the front side in the axis P direction and the rear side in the axis P direction of the rotating body 11 , the radial bearings support both ends of the rotating body 11 . Therefore, the radial load of the rotating body 11 can be held in a more stable manner.

A blood pump having an alternative structure will be described below. FIG. 4 is a schematic sectional view of a blood pump having an alternative structure according to the present embodiment. Regarding the blood pump having an alternative structure described below, elements that are equivalent to those included in the blood pump described above have the same reference numerals, and description will be made for differences therebetween.

This blood pump with an alternative structure differs from the blood pump described above in: the configuration of the shaft 11 B of the rotating body 11 in the pump unit 10 , the configuration of the bearing unit 12 B of the casing 12 that the shaft 11 B involves, the configuration of the rotating member 23 in the driving unit 20 , and the configuration of the lid member 24 that the rotating member 23 involves.

In the rotating body 11 of the pump unit 10 , the shaft 11 B is formed in an annular shape centering on the axis P, and projects further toward the rear side in the axis P direction of the rear shroud 11 A 2 . On the inner periphery of the shaft 11 B, the annular bearing surface 11 B 1 centering on the axis P is formed. The driven magnet 11 B 3 is also provided to the shaft 11 B. The driven magnet 11 B 3 is a permanent magnet and is embedded in the shaft 11 B along the bearing surface 11 B 1 . A plurality of such driven magnets 11 B 3 is formed in an annular shape centering on the axis P and is so arranged that S and N poles are alternately placed next to each other along the annular shape. On the center of the rear shroud 11 A 2 to which the shaft 11 B is provided protrudingly, the penetrating hole 11 B 2 is formed along the axis P. The penetrating hole 11 B 2 is provided to penetrate the rear shroud 11 A 2 and to communicate with the suction port 11 A 1 a of the front shroud 11 A 1 through the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 .

The casing 12 is formed to have a certain gap between its inner wall and the contour of the rotating body 11 . In other words, the casing 12 is configured to have a noncontact operation state with respect to the rotating body 11 while containing therein the rotating body 11 . On the inner wall of the bearing unit 12 B of the casing 12 , the annular bearing surface 12 B 1 centering on the axis P is placed face to face with the bearing surface 11 B 1 formed on the shaft 11 B of the rotating body 11 with a certain gap in the radial direction of the rotating body 11 interposed therebetween.

The rotating member 23 in the driving unit 20 is fixed to the output shaft 22 A of the driving motor 22 and provided rotatably about the axis P through driving of the driving motor 22 . The rotating member 23 is formed in a cylindrical shape centering on the axis P to come inside the annular shape of the bearing unit 12 B of the casing 12 . In other words, the rotating member 23 comes inside the annular shape of the shaft 11 B of the rotating body 11 .

To the cylindrical outer wall of the rotating member 23 , the drive magnet 23 A is provided. The drive magnet 23 A is a permanent magnet. A plurality of such drive magnets 23 A is formed in an annular shape centering on the axis P and is so arranged that S and N poles are alternately placed next to each other along the annular shape. The drive magnet 23 A is placed face to face with the driven magnet 11 B 3 in the radial direction of the rotating body 11 , thereby being magnetically coupled with the driven magnet 11 B 3 provided to the shaft 11 B of the rotating body 11 from outside of the casing 12 .

On the front side in the axis P direction of the container 21 , the lid member 24 is provided for hermetically closing the opening of the container 21 and covering the driving motor 22 and the rotating member 23 .

The lid member 24 has the recess 24 A in an annular shape surrounding the cylindrical shape of the rotating member 23 . Into the recess 24 A, the bearing unit 12 B of the casing 12 is inserted to place the shaft 11 B of the pump unit 10 outside the cylindrical shape of the rotating member 23 . The bearing unit 12 B of the casing 12 is detachably provided to the recess 24 A.

The blood pump thus configured drives, in a state where the bearing unit 12 B of the casing 12 is inserted into the recess 24 A of the lid member 24 , the driving motor 22 to cause the rotating member 23 to rotate about the axis P. When the rotating member 23 rotates, the drive magnet 23 A provided to the rotating member 23 rotates about the axis P. Along with this rotation, the driven magnet 11 B 3 magnetically coupled with the drive magnet 23 A also rotates. When the driven magnet 11 B 3 rotates, the rotating body 11 provided with the driven magnet 11 B 3 rotates substantially about the axis P. In this operation, because the driven magnet 11 B 3 is magnetically coupled with the drive magnet 23 A, suction force in the opposite direction to the movement in the axis P direction acts on the rotating body 11 provided with the driven magnet 11 B 3 . In other words, the driven magnet 11 B 3 and the drive magnet 23 A serve as a magnetic coupling functioning as an axial bearing that holds rotation of the rotating body 11 in the axis P direction.

When the rotating body 11 rotates, by the action of the vanes 11 A 3 , blood is taken inside the casing 12 through the suction inlet 12 A 1 . The blood is pumped through the suction port 11 A 1 a of the impeller 11 A into the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 , further pumped through this gap outward in the radial direction, and pumped outside the casing 12 through the ejection outlet 12 A 2 .

Part of the high-pressure blood pumped outward in the radial direction through the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 is not pumped outside the casing 12 through the ejection outlet 12 A 2 , and circulates in a comparatively low pressure area near the axis P inside the casing 12 . More specifically, on the outer periphery of the impeller 11 A, the high-pressure blood flows through the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 toward the front side of the front shroud 11 A 1 and the rear side of the rear shroud 11 A 2 . The blood flowing toward the front side of the front shroud 11 A 1 passes between the front surface of the front shroud 11 A 1 and the inner wall of the casing 12 toward the axis P, and returns to the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 through the suction port 11 A 1 a . On the other hand, the blood flowing toward the rear side of the rear shroud 11 A 2 passes between the rear surface of the rear shroud 11 A 2 and the inner wall of the casing 12 toward the axis P, further passes through the gap between the bearing surface 11 B 1 of the shaft 11 B and the bearing surface 12 B 1 of the casing 12 , and returns to the gap between the front shroud 11 A 1 and the rear shroud 11 A 2 through the penetrating hole 11 B 2 .

Because the gap between the bearing surface 11 B 1 and the bearing surface 12 B 1 is formed in an annular shape centering on the axis P, the blood passes through this gap, and the bearing surface 11 B 1 and the bearing surface 12 B 1 serve as a radial bearing as a dynamic bearing that holds rotation of the rotating body 11 about the axis P in the radial direction with the blood working as a lubricating fluid. In this manner, the shaft 11 B is held in a position centering on the axis P. In other words, the radial position of the rotating body 11 is held in a noncontact state with respect to the casing 12 .

Accordingly, with this blood pump, because the radial bearing and the axial bearing cause the rotating body 11 to rotate in a noncontact state with respect to the casing 12 , states leading to hemolysis or a blood clot can be prevented without the need for any shaft penetrating the casing 12 or any axial sealing structure to prevent leakage of blood along the shaft.

In particular, the impeller 11 A of the pump unit 10 in this blood pump includes the front shroud 11 A 1 arranged on the front side in the axis P direction through which blood is taken in, the rear shroud 11 A 2 arranged on the rear side in the axis P direction of the front shroud 11 A 1 , and the vanes 11 A 3 arranged between the front shroud 11 A 1 and the rear shroud 11 A 2 . Therefore, the blood flowing toward the rear side of the rear shroud 11 A 2 produces pressure acting on the front side in the axis P direction, and the blood flowing toward the front side of the front shroud 11 A 1 produces pressure acting on the rear side in the axis P direction. Consequently, the axial thrust load pushing the impeller 11 A in the axis P direction can be adjusted, whereby defective operation is prevented with a simple axial bearing having the driven magnet 11 B 3 and the drive magnet 23 A alone. Manufacturing cost can be thus reduced because no control circuit for adjusting the magnetic force of a magnet core is required.

With this blood pump, the pump unit 10 is detachably provided to the driving unit 20 . The pump unit 10 , which comes in contact with blood, is thus disposable as a consumable supply. By providing the pump unit 10 that is economical with this configuration, running cost to purchase consumable supplies can be reduced.

The blood pump according to the present embodiment includes a radial bearing each on the front side in the axis P direction and the rear side in the axis P direction of the rotating body 11 . The radial bearing on the rear side in the axis P direction of the rotating body 11 is, as described above, the gap between the bearing surface 11 B 1 and the bearing surface 12 B 1 that is placed between the driven magnet 11 B 3 and the drive magnet 23 A. The radial bearing on the front side in the axis P direction of the rotating body 11 is arranged on the front side of the front shroud 11 A 1 , except for between the driven magnet 11 B 3 and the drive magnet 23 A. More specifically, on the front side of the front shroud 11 A 1 , a cylindrical unit 11 A 1 b is formed to extend further toward the front side of the suction port 11 A 1 a . On the outer periphery of the cylindrical unit 11 A 1 b , an annular bearing surface 11 A 1 c centering on the axis P is provided. On the other hand, on the inner wall of the pumping unit 12 A of the casing 12 , an annular bearing surface 12 A 3 centering on the axis P is placed face to face with the bearing surface 11 A 1 c with a certain gap in the radial direction of the rotating body 11 interposed therebetween. The blood passes through the gap between the bearing surface 11 A 1 c and the bearing surface 12 A 3 , and the bearing surface 11 A 1 c and the bearing surface 12 A 3 serve as a radial bearing as a dynamic bearing that holds rotation of the rotating body 11 about the axis P in the radial direction with the blood working as a lubricating fluid. In this manner, the impeller 11 A is held in a position centering on the axis P. By thus providing the radial bearings on the front side in the axis P direction and the rear side in the axis P direction of the rotating body 11 , the radial bearings support both ends of the rotating body 11 . Therefore, the radial load of the rotating body 11 can be held in a more stable manner.

As described above, the blood pump and the pump unit according to the present invention are configured to rotatably support an impeller in a casing in the radial direction in a noncontact manner and to support axial thrust load at low manufacturing cost, thereby suitable for enabling rotation also in the axial direction in a noncontact manner.